Intraocular lens comprising drug-containing microspheres

ABSTRACT

An intraocular lenses having a plurality of drug-containing microspheres attached to the intraocular lens. The intraocular lenses can be used for patients undergoing cataract surgery and reduces the need for recurrent surgery, follow-up treatment or postoperative eye-drops. Also provides a method for manufacturing such an intraocular lens and the use of an intraocular lens in the treatment of cataract.

TECHNICAL FIELD OF THE INVENTION

The present invention provides intraocular lenses with drug-containingmicrospheres attached to the intraocular lens, preferably attached toone or more haptics of the intraocular lens. The microspheres may beconfigured to release a drug in a defined manner when the intraocularlens is inserted in an animal eye. Said intraocular lenses can thus beconsidered as intraocular lenses having controlled drug release, ordrug-eluting intraocular lenses. Such intraocular lenses can be used forpatients undergoing cataract surgery and reduces the need for recurrentsurgery, follow-up treatment or postoperative administration ofeye-drops.

Intraocular lenses (IOL) are lenses implanted in the eye used to treatcataracts or myopia.

The most common type of intraocular lens is the pseudophakic intraocularlens. These are implanted during cataract surgery, after the cloudycrystalline lens (otherwise known as a cataract) has been removed. Thepseudophakic intraocular lenses replace the original crystalline lens,and provide the light focusing function originally undertaken by thecrystalline lens.

The second type of intraocular lenses, more commonly known as a phakicintraocular lens (PIOL), is a lens which is placed over the existingnatural lens, and is used in refractive surgery to change the eye'soptical power as a treatment for myopia or nearsightedness.

Intraocular lenses usually consist of a small plastic lens with plasticside struts, called haptics, to hold the lens in place within thecapsular bag inside the eye.

Insertion of an intraocular lens for the treatment of cataracts is themost commonly performed eye surgical procedure. Surgeons annuallyimplant more than 6 million lenses. The procedure can be done underlocal anesthesia with the patient awake throughout the operation. Theuse of a flexible intraocular lens enables the lens to be rolled forinsertion into the capsule through a very small incision, thus avoidingthe need for stitches, and this procedure usually takes less than 30minutes in the hands of an experienced ophthalmologist. The recoveryperiod is about 2-3 weeks. After surgery, patients should avoidstrenuous exercise or anything else that significantly increases bloodpressure.

Cataract is defined as opacification of the lens within the eye and isthe commonest cause of blindness worldwide. Cataract surgery is thecommonest surgical procedure performed in the developed world. Despiteadvances in laser technology and micro-incision surgical platforms,cataract surgery still carries three main risks of: (1) postoperativeintraocular inflammation, (2) infection, (3) secondary opacification ofthe lens capsule, known as posterior capsular opacification (PCO) and(4) glaucoma. If PCO develops, a further procedure, in the form of alaser is required.

Cataract extraction and implantation of an artificial intraocular lens(IOL) can restore patients' vision. After surgery, patients are requiredto administer eye drops, containing antibiotic and steroids, to reducethe risk of inflammation and infection. However, this requires goodpatient compliance, which may not be achievable in elderly patients witharthritis and other medical problems. Untreated intraocular inflammationleads to pain, redness, and retinal swelling, which can cause blurredvision. Post-operative infection, although rare, can result incatastrophic visual loss. The commonest complication after cataractsurgery is posterior capsular opacification (PCO), which occurs inaround 25% of patients. This is caused by proliferation of residual lenscells across the lens capsule, leading to a gradual deterioration invision, and requires a further procedure for the successful treatment.

There are currently 300,000 lens replacement surgeries carried out bythe NHS (National Health Service England) each year and another 100,000in the private sector. Due to an ageing population, the rate of cataractsurgery is increasing. There is currently a lot of interest in betterand more effective treatments for cataracts.

PRIOR ART

Studies investigating whether a specific drug is useful for reduction ofinflammation post cataract surgery are known. For example, one paperdeals with the reduced inflammation on the first postoperative day aftercataract surgery in eyes with and without glaucoma (cf. Diane TW Chang,“Intracameral dexamethasone reduces inflammation on the firstpostoperative day after cataract surgery in eye with and withoutglaucoma”, in Clinical Ophthalmology, 2009:3, 345-355).

Directly coated drugs have the problem that drugs, such as cyclosporineA (CsA) are hydrophobic compounds with a large molecular weight andtheir permeability in eyes is poor. Therefore, its concentration inaqueous humor and other tissues is relatively low compared to therequired therapeutic concentration, affecting its topical therapeuticeffects. It has been shown that only 8% of CsA in eye drops reachcorneal endothelium, only 1% reaches the anterior chamber, with theconcentration in the posterior chamber, such as aqueous humor andvitreous far less than the required therapeutic level. Also, a hugepercentage of drugs given through conventional administration lose theireffects due tear drainage, absorption of nasopharyngeal mucosa and otherfactors.

One investigation studies the combination of phenylephrine/ketorolacinjection as medication for use in cataract surgery (cf. L. El. Lawuyi,“The clinical utility of new combination phenylephrine/ketorolacinjection in cataract surgery”, in Clinical Opthalmology, 2015; 9,1249-1254). The drawback of such a direct injection is the discomfortfor the patient, as the injection has to be frequently renewed, as wellas difficult control of the amount of injected drug.

Regarding intraocular lenses comprising releasable drugs, reference ismade to CN 104434811 A, US 2009/130176 A, US 2010/016439 A, US2012/191185 A, WO 12/021107 and US 2010/074942 A.

The present invention aims to solve the above-mentioned problems, i.e.aims at setting aside the complications occurring when commonintraocular lenses are implanted, in particular for the treatment ofcataract. Often, patients are required to administer eye drops afterinsertion of the intraocular lens on a regular basis, leading todecreased patient acceptance. If the patients do not administer the eyedrops, or administer them on an irregular basis, this may lead tointraocular inflammation, pain, redness, and retinal swelling, which cancause blurred vision. On the other hand, when eye drops are administereddirectly onto the cornea or injected into the eye, this has to be doneon a regular basis and the amount of drug actually reaching the targetarea can be hardly controlled. Also, the drugs may diffuse onto thepupilla, causing cloudy vision or visual impairment.

If as posterior capsular opacification develops, laser treatment isrequired. Laser treatment is a further procedure that is expensive forhealthcare commissioners and requires an additional visit. Furthermoreit has been associated with retinal detachment, damage to the lensoptic, creation of floaters, and inducing retinal swelling (maculaoedema). Therefore laser treatment should be avoided, if possible. Also,laser treatment can be hardly performed on animals, such as cats ordogs, as the procedure is commonly done under local anesthesia with thepatient awake and upright throughout the procedure. However, animals, inparticular cats or dogs, tend to move during such a procedure, and it isparticularly difficult to achieve the fine focus required to achievesuccess with laser treatment in animals, such that the success of alaser treatment post-introduction of an IOL is very low and the risk tocause damage to the patient with the laser is very high.

In view of the above drawbacks and disadvantages, the present inventionhas been developed.

Short Description of the Invention

The present invention provides an intraocular lens, comprising aplurality of drug-containing microspheres attached to the intraocularlens. The intraocular lens may comprise an optic and at least onehaptic. The microspheres can be attached to one or more haptics and/orthe optic of the intraocular lens. The microspheres may be configured torelease a drug in a defined manner when the intraocular lens is insertedin an animal eye. Animal in the context of the present applicationincludes mammals, such as humans.

In a preferred embodiment, the intraocular lens includes a plurality ofhaptics, i.e. at least two haptics.

In a further preferred embodiment, the drug-containing microspheres areattached to each of the plurality of haptics. In a further preferredembodiment, the drug-containing microspheres are attached to each of theplurality of haptics as well as the optic.

A preferred way of attaching is done by covalently bonding themicrospheres to the intraocular lens (e.g the haptics). The microspheresmay be attached by using an acid or an amine group that forms an amidegroup. In this way, an amide bond can form between the amine group onthe microspheres and the acid group on the intraocular lens, or betweenthe acid group on the microspheres and the amine group on theintraocular lens.

In a further preferred embodiment, an optic of the intraocular lens isfree of drug-containing microspheres. The microspheres may thus beattached only to the least one haptic of the intraocular lens, i.e. theymay not be attached to the optic of the intraocular lens. In otherwords, in this embodiment, the optic will be free from attachedmicrospheres.

At least some of the plurality of drug-containing microspheres maycontain different drugs and/or may have different sizes.

The microspheres may have properties that allow controllably releasingor releasing in a defined manner a drug contained in the microspheres.Such an effect can be achieved by biodegradable microspheres, i.e.microspheres that are formed of a material comprising at least onebiodegradable material such as a polymer. Particularly preferredmaterials that may be used according to the present invention arepoly(L-lactic acid) and poly(lactic-co-glycolic acid), which areconsidered to have biodegradable properties.

The intraocular lens preferably may comprise at least one materialselected from acrylates (such as polymethylmethacrylate (PMMA)),silicone (such as polydimethylsiloxane (PDMS)), hydrophobic acrylate,hydrophilic acrylate and collamer.

The one or more haptics may comprise at least one material selected fromacrylates (such as poly(methyl methacrylate) (PMMA)), fluorinatedpolymers (such as polyvinylidene fluoride (PVDF)), polyimide(elastimide), and polyolefins (such as polypropylene (prolene)). In apreferred embodiment, the haptics may thus comprise at least onematerial selected from PMMA, PVDF, polyimide or polypropylene.

The optic and the one or more haptics of the intraocular lens maycomprise the same or a different material.

The plurality of drug-containing microspheres may comprise or includemicrospheres containing at least one drug selected from antibiotics,anti-inflammatory, anti-hypertensive, anti-glaucoma andanti-proliferative agents. The microspheres may contain furthermaterials such as solvents in which the drug are dissolved. Thus, theterm drug-containing microspheres refers to microspheres at leastcontaining drugs, but also containing other materials with which thedrugs are commonly associated, in particular solvents.

The present invention also provides a method for manufacturing anintraocular lens according to the present invention, the methodcomprising steps of:

i) providing drug-containing microspheres;ii) providing a precursor intraocular lens;iii) activating the microspheres and/or the precursor intraocular lens;andiv) attaching the microspheres to the precursor or activated intraocularlens. The microspheres may be attached to at least one or more hapticsof the precursor or activated intraocular lens.

The providing the drug-containing microspheres may include preparing themicrospheres by a solvent evaporation method.

The activating the microspheres may include applying an acid or a baseto the microspheres. In a preferred embodiment one of an acid group,sodium hydroxide and a diamino linker may be applied to themicrospheres.

The attaching the microspheres may include reacting one of an acid groupand an amine group on the microspheres with one or more reactive groupson the precursor or activated intraocular lens.

The one or more haptics may have an open-loop design, a hapticangulation design or monobloc-plate style design.

The intraocular lens according to the present invention may particularlybe used for the treatment of cataract. In a further preferredembodiment, the intraocular lens according to the present invention maybe used for the treatment of glaucoma.

The intraocular lens can particularly be used in humans. The intraocularlens can also preferably be used in animals, in particular cats, dogsand horses.

The present invention also provides a method for cataract treatment,comprising: providing an intraocular lens including a plurality ofdrug-containing microspheres attached to the intraocular lens (e.g.attached to one or more haptics of the intraocular lens); inserting theintraocular lens into a capsular bag of an eye to be treated; andcausing one or more drugs contained in the microspheres to be releasedinto the eye. The present invention also provides a use of anintraocular lens according to the present invention for the treatment ofcataract or glaucoma. The present invention also provides a method forthe treatment of cataract or glaucoma, comprising the steps of: i)removal of the natural lens of the eye, and ii) inserting an intraocularlens according to the present invention into the eye.

BRIEF DESCRIPTION OF THE FIGURES

FIG. 1 shows a schematic illustration of an intraocular lens accordingto the present invention, wherein the microspheres are attached to thehaptics of the intraocular lens.

FIG. 2 is a schematic illustration of a method for manufacturing anintraocular lens with attached microspheres.

FIG. 3 shows a schematic illustration of preparation of microspheres bythe solvent evaporation technique.

FIG. 4 show scanning electron micrographs of 50:50 PLLA:PLGAmicrospheres prepared using the solvent evaporation technique (A)Original magnification×600; (B) Original magnification×2700.

FIG. 5 shows an example of varying degradation times for microspheres,illustrating how the release times can be tuned using different ratiosof the two polymers. Rhodamine B was encapsulated and release measuredpercentage of the total Rhodamine encapsulated.

DETAILED DESCRIPTION OF THE INVENTION

The present invention solves the above problems by providing anintraocular lens (IOL), comprising a plurality of drug-containingmicrospheres attached to the intraocular lens. The intraocular lens maycomprise an optic and at least one haptic. The microspheres can beattached to one or more haptics and/or the optic of the intraocularlens. In a preferred embodiment, the intraocular lens comprises at leasttwo haptics. In the present invention, the term “microspheres” denotesdrug-containing microspheres. The drug-containing microspheres maycomprise at least a drug and a solvent.

In a preferred embodiment, the microspheres are configured to release adrug in a defined manner when the intraocular lens is inserted in ananimal eye. The release of a drug in a defined manner may be understoodas the controlled release of the drug over a prolonged period of time.The defined release bay thus be understood as controlling the release byexternal factors, such as the eye pH.

The intraocular lens may thus be provided with a plurality ofmicrospheres attached to the one or more haptics and/or the optic,wherein the microspheres comprise at least one drug and are configuredto release the at least one drug.

In a preferred embodiment, the intraocular lens includes a plurality ofhaptics, i.e. at least two, three or four haptics. In a particularlypreferred embodiment, the intraocular lens includes two haptics. Thehaptics may be arranged on opposite sides of the optic of theintraocular lens. The one or more haptics may have an open-loop design,a haptic angulation design or monobloc-plate style design.

In a further preferred embodiment, the drug-containing microspheres areattached to each of the one or more haptics. In a preferred embodiment,an optic of the intraocular lens is free of drug-containingmicrospheres. The microspheres may thus be attached only to the leastone haptic of the intraocular lens, i.e. they are not attached to theoptic of the intraocular lens. In other words, in this embodiment, theoptic will be free from attached microspheres.

In another preferred embodiment, at least some of the plurality ofdrug-containing microspheres contain different drugs and/or havedifferent sizes.

It is noted that the term microspheres generally refers to spherialmicroparticles, but may also include microparticles not having a perfectspherical shape. Microspheres are small spherical particles, withdiameters in the micrometer range (typically 1 μm to 1000 μm (1 mm)).Microspheres are sometimes referred to as microparticles. Microspherescan be manufactured from various natural and synthetic materials. Glassmicrospheres, polymer microspheres and ceramic microspheres arecommercially available. Solid and hollow microspheres vary widely indensity and, therefore, are used for different applications. Hollowmicrospheres are typically used as additives to lower the density of amaterial.

The microspheres may comprise at least one outer polymeric layer thatforms the shape of the microsphere. The microspheres may be consideredas generally hollow (even though substances such as a drug may becomprised) and may comprise at least one drug. In a preferredembodiment, the microspheres comprise at least a drug and a solvent. Inthe present invention, a microsphere may contain one drug or severaldifferent drugs. The intraocular lens may thus comprise a plurality ofdrug-containing microspheres, each containing more than one differentdrug. The intraocular lens may also have two or more differentmicrospheres attached, wherein a first set of drug-containingmicrospheres contains one drug and a second set of drug-containingmicrospheres contains a different drug.

The microspheres may have different sizes. Microspheres defined by aspecific size may exist in a size-range, i.e. the specific size providedmay define an average size. The microspheres preferably have a sizebelow 100 μm. The microspheres in the present invention may have a sizein the range of 1-100 μm, more preferably of 1-50 μm, and even morepreferably from 1-20 μm. In a preferred embodiment, the microspheres mayhave a size in the range of 2-100 μm, 10-100 μm-20-100 μm or 20-50 μm.The size of the microspheres may be measured by scanning electronmicroscope (SEM). SEM allows the easy measurement of microspheresattached to an intraocular lens.

When microspheres being <100 micrometer in diameter are used, this hasthe advantage that they fit into an injector syringe and into the lenscapsule without causing unintentional drug release from the microspheresor cause the microspheres to become detached during insertion into thelens capsule.

The drug-containing microspheres may be configured to controllablyrelease the at least one drug into an animal eye. The controlled releasemeans that the drug is administered to the patient over a prolongedperiod of time, such as for at least one month. The release of drugsthat can be detected in the UV-Vis region of the light spectrum can bemeasured by UV-Vis spectroscopy. Otherwise, biological assay or taggingof the drugs enables the detection thereof. Corresponding assays andmeasurement methods are known in the art. The measurement can also bedone by determining the biological response, i.e. by measuring theintraocular inflammation of the eye, e.g. by assessing the anteriorchamber cellular response and the anterior chamber “flare”, which iscaused by protein exudation. Alternatively, it is feasible to takesamples of fluid from the front of the eye and measure the concentrationof the samples.

In a preferred embodiment, the drug-containing microspheres are formedof biodegradable material. Biodegradability in the context of thepresent invention is regarded as the degradation within the eye in aperiod of 1 week to 12 months, preferably within 6 months, even morepreferably within 4 months, depending on what drug has beenencapsulated.

Biodegradation in the eye is understood as the degradation of themicrospheres in the eye medium. The microspheres may be seen as fullydegraded when all of the contained drugs have been released.

The release may be controlled by adjusting the PLLA:PLGA ratio, theaverage molecular weight of the PLGA and PLGA polymers, the encapsulateddrug, the size of the microspheres, the ratio of the glycolic acids tolactic acid monomers present in the PLGA, the PLGA/PLLA polymer endgroups and the crystallinity.

An intraocular lens configured to release a drug in a defined manner orin a controlled manner enables that the patient or practitioner does nothave to administer drugs manually, e.g. by way of eye drops orinjection, post-insertion of the intraocular lens. In view of theintraocular lens being able to release drugs over an extended period oftime, such as for at least 1 week, 2 weeks, 1 month, 2 months, 3 months,4 months, 5 months, 6 months or 1 year, in particular for at least 2 to6 weeks, 4 months or 6 months, there is no need for administering eyedrops to the eye. Thus, the intraocular lenses are configured to releasedrugs for at least 1 week, 2 weeks, 1 month, 2 months, 3 months, 4months, 5 months, 6 months, 1 year, in particular for at least 2 to 6weeks, 4 months or 6 months. The skilled artisan will be able to definethe required period of time based on the experience with theadministration of eye drops to patients having undergone regular surgerywith insertion of an intraocular lens. Thus, if, based on experience,eye drops are administered for 4 months to a patient, than theintraocular lens should be configured to release drugs for about 4months.

Controlled release or release in a defined manner in the context of thepresent invention is understood as the delivery of compounds (such asdrugs) in response to time. The timed release in the present inventionis regarded as sustained release, i.e. release over a prolonged periodof time. The defined release not only prolongs action, but it maintainsdrug levels within the therapeutic window to avoid potentially hazardouspeaks in drug concentration following introduction of the intraocularlens and to maximize therapeutic efficiency.

Antibiotic release may be required for the first two weeks of thesurgery, with a peak release at 2-5 days after surgery, as this is thetime at which the infection is most likely to occur. Thus, an antibioticdrug may be released for at least 1 day to 1 month, 2 days to 1 month, 2days to 2 weeks, 5 days to 2 weeks, or preferably 1 day to two weeks.

Anti-inflammatory drug release may be required for a duration of atleast 1 week to 2 months, 1 week to 2 months or preferably for 4 to 6weeks.

Anti-PCO drug release may be required for approximately 4-6 months, orpossibly longer. Anti-PCO drugs may thus be released for 1 month to 1year, 1 to 6 months, 2 to 6 months or preferably at least 4 to 6 months.

Anti-hypertensive drug release may be required for approximately 1 to 3months, therefore anti-hypertensive drugs that are encapsulated intomicrospheres and attached to the IOL may be released for 2 weeks to 4months.

The required drug concentrations differ depending on the drug. The drugconcentrations can be provided as amount in mg per ml of solventcontained in the microspheres. The concentrations for the drugs may be:

For antibiotic drugs, such as intracameral antibiotic drugs (e.g.cefuroxime), the concentration in the drug-containing microspheres maybe from 0.1 to 10 mg/0.1 ml, preferably from 0.2 to 5 mg/0.1 ml, evenmore preferably from 0.5 to 2.0 mg/0.1 ml, and even more preferablyabout 1.0 mg/0.1 ml.

For anti-inflammatory drugs, such as intracameral anti-inflammatorydrugs (e.g. dexamethasone), the concentration in the drug-containingmicrospheres may be from 0.1 to 10 mg/0.1 ml, preferably from 0.2 to 5mg/0.1 ml, even more preferably from 0.5 to 2.0 mg/0.1 ml, and even morepreferably about 0.4 mg/0.1 ml. For the non-steroidal anti-inflammatorydrugs (NSAID) (e.g. ketorolac), the concentration in the drug-containingmicrospheres may be up to 0.5 mg/0.1 ml.

For anti-PCO drugs, such as intraocular anti-PCO drugs (e.g.cyclosporine), the concentration in the drug-containing microspheres maybe from 0.1 to 10 mg/0.1 ml, preferably from 0.2 to 5 mg/0.1 ml, evenmore preferably from 0.5 to 2.0 mg/0.1 ml, and even more preferably from1.0 to 1.5 mg/0.1 ml. 0.3-0.5 g in total of anti-PCO drugs may bereleased over a 6 month period. As comparison, typical concentrations ofeye-drops administered after surgery include: dexamethasone eye drops(0.1%) four times a day and cefuroxime 5% (i.e. 50 mg/ml) eye drops fourtimes a day.

Higher doses than that usually used for eyedrops can be used, as therelease of the drugs is controlled over a prolonged period of time.

The intraocular lenses commonly comprise a small plastic lens withplastic side struts or arms, called haptics, to hold the lens in placewithin the capsular bag inside the eye.

The optical portion of the lens, also usually simply called “optic” andalso referred to as “lens portion” is usually a round biconvex structurewhich is usually slightly vaulted posteriorly.

The haptics are configured to stabilize the intraocular lens within theeye after insertion therein. The haptics can have an open-loop design,haptic angulation design, monobloc-plate style design or another specialdesign. Typical designs for the haptics are disclosed in “AchievingExcellence in Cataract Surgery—A Step-by-Step Approach”, Edited by D. M.Colvard, Chapter 12 “Intraocular lens materials and design”, pages 95 to108, 2009.

One particularly preferred shape of the haptics is the open-loopmultipiece design. Open-loop intraocular lenses are held in place in thecapsule bag by exerting a centripetal pressure on the capsule bag fornixand sometimes also the ciliary body, or in case of sulcus placement theciliary sulcus. The haptics of an intraocular lens should maintain theiroriginal configuration during the implantation procedure. The hapticrigidity, which is the resistance of the haptic to forces that bend theloops centrally, and the haptic memory, which is the ability of thehaptic to go back to its original configuration after having been bent,are the two factors that determine whether an intraocular lens willcenter well in an eye after implantation. Additionally, the contractiveforces of the shrinking capsule bag due to fibrosis, especially in caseswith zonule weakness or asymmetric shrinking, will need counteractingpressure from the haptics to ensure good centration.

Haptic materials that can be used in this invention are acrylates,fluorinated polymers, polyimides and polyolefins. Preferred materialsare thus poly(methyl methacrylate) (PMMA), polyvinylidene fluoride(PVDF), polyimide (elastimide), and polypropylene (prolene).Particularly preferred are poly(methyl methacrylate) (PMMA) andpolyimide.

The j-loop design results in pinpointed contact with the capsule bagequator, which may lead to stress folds of the posterior capsule, whichusually disappear within the first months after surgery concomitant withthe decrease in memory of the haptic material and this type of loop isthe preferred type for intraocular lenses dedicated for sulcusplacement.

The optic (lens portion) can be a flexible UV-blocking hydrophobic orhydrophilic acrylic with round or square edges, seamlessly joined to, orattached to, UV-blocking hydrophobic or hydrophilic acrylic haptic loopsor haptic plate.

In the invention, the intraocular lens comprises microspheres that areattached to the intraocular lens (e.g. attached to at least one hapticof the intraocular lens). The microspheres contain at least one drug.The drug is contained in the inside of the microspheres and may bereleased in a defined manner over a prolonged period of time, e.g. asthe microspheres are degraded.

The material of the microspheres can be any polymer that isbiodegradable. Biodegradability in the context of the present inventionis regarded as the degradation within the eye in a period of 1 week to12 months, preferably within 6 months, even more preferably within 4months.

Particularly preferred polymer materials according to the presentinvention are poly(L-lactic acid) (PLLA) and poly(lactic-co-glycolicacid) (PLGA) due to their biodegradability and biocompatibility. Themicrospheres of the present invention may comprise or be formed of amaterial comprising at least one polymer selected from poly(L-lacticacid) (PLEA) and poly(lactic-co-glycolic acid) (PLGA). It is noted thatmicrospheres may in this particular case be defined in technical termsby the ratio of PLLA to PLGA. These biodegradable polymers haveregulatory approval for human clinical use and have the advantage thattheir degradation can be tuned based on the ratio of different monomerunits present. Depending on the drug and release rates required, themicrospheres will comprise a mixture of poly(lactic-co-glycolic acid)(PLGA) and poly(L-lactic acid)(PLLA).

FIG. 5 shows an example of varying degradation times for microspheres,illustrating how the release times can be tuned using different ratiosof the two polymers. Rhodamine B was encapsulated and release measuredpercentage of the total Rhodamine encapsulated. The results wereobtained by UV-Visible spectroscopy plotted against a calibration graph.

Biodegradability is commonly understood as the chemical dissolution ofmaterials by bacteria, fungi, or other biological means. In the contextof the present invention, biodegradability of the microspheres meansthat the microspheres will be degraded over a prolonged period of timein the eye medium.

The attachment to the intraocular lens will be defined further downbelow with respect to an embodiment in which the microspheres areattached to the haptics.

Types of drugs that may be used in the present invention and that areslowly and controllably released or released in a defined manner withinthe eye are antibiotics, anti-inflammatory agents, anti-hypertensive andanti-proliferative agents.

The microspheres contain physiologically relevant concentrations ofdrugs. The required drug concentrations differ depending on the drug.Typical concentrations may lie in the range of 0.1 to 10 mg/0.1 ml,preferably from 0.2 to 5 mg/0.1 ml, even more preferably from 0.5 to 2.0mg/0.1 ml, and even more preferably about 0.5 to 1.0 mg/0.1 ml.

Typical solvents in which the drugs can be dissolved are known to theskilled person. Commonly, the solvents are identical to those usedduring the formation of the microspheres.

The drugs are released into the lens capsule over a period of up to atleast 1 week, 2 weeks, 1 month, 2 months, 3 months, 4 months, 6 monthsor 1 year.

The invention thus provides a biodegradable polymer-based drug elutionsystem (i.e. drug-containing microsphere) which can be attached to theintraocular lens, allowing slow and controlled release of antibiotics,anti-inflammatory, anti-proliferative or anti-hypertensive drugs withinthe eye.

Antibiotics may be selected from tacrolimus, sirolimus, everolimus,cyclosporine, and ascomycin, or mycophenolic acid.

Other drugs that may be included are cyclosporine to prevent PCO,carbonic anhydrase inhibitors or Apraclonidine as hypotensive agents,dexamethasone, a steroidal anti-inflammatory agent, ketorolac ornepafenac as non-steroidal inflammatory agents and the antibioticscefuroxime and/or vancomycin.

Anti-PCO drug in the context of the present invention comprise drugsthat are able to prevent PCO. The anti-PCO drugs may also have otheradditional properties, such an antibiotic or anti-inflammatory effect.

The microspheres may thus contain at least one of tacrolimus, sirolimus,everolimus, cyclosporine, ascomycin, mycophenolic acid, cyclosporine,dexamethasone, ketorolac or nepafenac, cefuroxime and/or vancomycin or acombination of any of these drugs.

The microspheres may be configured to release at least an antibiotic, ananti-inflammatory drug and an anti-PCO drug. In a preferred embodiment,the microspheres may contain all three types of drugs. In a further evenmore preferred embodiment, several microspheres, each containing adifferent type of drug may be used.

The microspheres of the present invention are attached to theintraocular lens. In a preferred embodiment, the microspheres areattached to haptics of the intraocular lens. In an even furtherpreferred embodiment, the microspheres are only attached to the hapticsof the intraocular lens. One such intraocular lens with microspheresonly attached to the haptics is depicted in FIG. 1. In this Figure, anintraocular lens is generally designated 10 and includes a central optic12 and a plurality of haptics 14 extending sideways (laterally) from thecentral optic 12. In the example case shown in FIG. 1, the plurality ofhaptics 14 are a pair. Among the pair, one haptic may serve as a leadinghaptic whereas the other haptic may serve as a trailing haptic. It is tobe understood that the total number of haptics 14 is not limited to twoin the present invention and that the intraocular lens 10 may compriseany number of haptics 14 larger or smaller than two as may be necessaryand useful to accomplish the goal of a secure and reliable placement ofthe intraocular lens 10 within a capsular bag of an eye to be treated.

In the embodiment of FIG. 1, a plurality of drug-releasing microspheres16 are attached to the intraocular lens 10 in the region of the pair ofhaptics 14, but not in the region of the central optic 12. In otherembodiments, not all of the haptics 14 are provided with thedrug-releasing microspheres 16. For example, one of the pair of haptics14 of the intraocular lens 10 shown in FIG. 1 may be left free of thedrug-releasing microspheres 16, so that all microspheres are provided inthe region of the other of the pair.

When the microspheres are only attached to the haptics 14 of theintraocular lens and not the central portion or optic 12, this preventsand cloudy vision or visual impairment. Thus, compared to eye drops thatdiffuse into the eye or intraocular lenses that provide drugs over theirwhole surface, the attachment to the haptics only has theabove-described advantage of no cloudy vision or visual impairment.

In a preferred embodiment, the microspheres are covalently bond to theintraocular lens. In a further preferred embodiment, the microspheresare attached via an acid or an amine group.

The attachment may be performed as described in the following. Once thedrug has been encapsulated the surface of the microsphere can be reactedto allow for reaction onto the intraocular lens at a later stage. Themicrospheres may be activated first. Activation means that themicrospheres are reacted and prepared for the attachment to theintraocular lens or haptics of the intraocular lens.

In one route, sodium hydroxide may be used to break the polymerstructure of the microspheres to form an acid group which can be reactedfurther (Scheme 1A). In another route, a diamino linker may be used,which activates the surface to give a free amine which can be reactedfurther (Scheme 1B).

The first route enables to react onto any amine using “typical peptidecoupling techniques”. The second round enables to react onto ester, acylchlorides, amides, anhydrides, carboxylic acids or alcohol groupspresent on the polymer.

Thus, the intraocular lens can firstly be broken down using acidicconditions and then the free acid chains on the intraocular lens can becoupled to the microspheres. Alternatively additional base can be addeddirectly to the lens, which ensures that the primary group on themicrosphere remains basic and can be reacted directly with theintraocular lens material. In the second route, the reactive group onthe microspheres can be used to react with the intraocular lens. Theselenses may comprise acrylic material, and are susceptible to hydrolysisdue to the esters present. The intraocular lens can firstly be brokendown using acidic conditions and then the free acid chains can becoupled to the microspheres using addition of base.

Reference is made to Y. Zhu et al, China Chem, 2012, 55, 2419-2427,which gives an example of activation by use of non-polar alcohols orsmall diamines to accelerate animolysis thereby creating primary —NH2groups on a poly caprolactone (PCL) polymer.

In a preferred embodiment, the microspheres may thus be attached via alinker comprising an acid group or an amine group. The linker may thuscomprise acid or amine groups and an alkyl chain.

In a further preferred embodiment of the present invention, the materialof the intraocular lens is selected from polymethylmethacrylate (PMMA),silicone (e.g. PDMS), hydrophobic acrylate, hydrophilic acrylate andcollamer. The optic, the one or more haptics and both the optic andhaptics may be formed of these materials. Preferred materials are thosethat allow having a flexible intraocular lens, as this enables the lensto be rolled for insertion into the capsule through a very smallincision, thus avoiding the need for stitches.

In a preferred embodiment, the intraocular lens is provided as aone-piece lens, i.e. where haptics and the optic are made from the samepiece of material (e.g. acrylic). In another preferred embodiment, theintraocular lens is provided as a multi-piece lens, i.e. wherein the atleast one haptic may be embedded into the body of the optic at thehaptic-optic junction.

Polymethylmethacrylate (PMMA) has been used successfully in intraocularlenses. It has been shown that PMMA material did does show any rejectionor foreign body reaction.

Silicone and acrylic are soft foldable inert materials. This allows thelens to be folded and inserted into the eye through a smaller incision.Specifically, acrylic lenses are a better choice in people who have ahistory of uveitis, or are likely to have to undergo retinal surgeryrequiring vitrectomy with replacement by silicone oil, such as personswith proliferative diabetic retinopathy or who are at high risk ofretinal detachment, such as persons with high myopia. Thus, in aparticularly preferred embodiment, the intraocular lens material isselected from silicon. In a further particularly preferred embodiment,the intraocular lens material is selected from acrylate.

One particular material for hydrophilic intraocular lenses is thetrademarked “Natural Yellow”. An intraocular lens material canincorporate the same UV-A blocking and violet light filteringchromophore that is present in the human crystalline lens. This materialprovides the exact chromophore the human retina naturally has for lightprotection.

Collamer is composed of collagen and copolymer material, is“bio-compatible” with the eye and contains up to 40% water.

In a preferred embodiment, the plurality of drug-containing microspheresinclude drug-containing microspheres containing at least one drugselected from antibiotics, anti-inflammatory agents, anti-hypertensiveagents and anti-proliferative agents.

In a further preferred embodiment, the intraocular lens of the presentinvention is used for the treatment of cataract, i.e. as pseudophakicintraocular lens. It is noted that the intraocular lens can also be usedas a lens which is placed over the existing natural lens, to change theeye's optical power as a treatment for myopia or nearsightedness, i.e.as phakic intraocular lens. The advantages of controlled release ofdrugs post-insertion can be beneficial for both kinds of intraocularlenses, i.e. for those used for the treatment of cataract and those forthe correction of myopia. Nevertheless, in view of the manycomplications that may occur during the treatment of cataract, theintraocular lenses intraocular lens according to the present inventionare particularly preferred for use in the treatment of cataract.

The intraocular lenses according to the present invention set aside thecomplications occurring when common intraocular lenses are implanted.One the one hand, patients are no longer required to administer eyedrops after insertion of the intraocular lens on a regular basis,leading to increased patient acceptance. Also, there is no risk offorgetting to administer the eye drop, as the drugs are administeredautomatically in a defined manner over the required period of time.Thus, the risk of intraocular inflammation, pain, redness, and retinalswelling, which can cause blurred vision is considerably reduced.

When the microspheres are attached to the intraocular lens or thehaptics of the intraocular lens, this prevents cloudy vision or visualimpairment that may occur with common intraocular lenses or when eyedrops are administered to the patient. Thus, the microspheres arepreferably only attached to the at least one haptic and not to theoptic.

If as posterior capsular opacification develops, laser treatment isrequired. This additional and annoying treatment can be prevented byusing the intraocular lenses of the present invention. Following theintraocular insult from surgery, lens epithelial cells can proliferatealong the haptic and optic or along the posterior capsule. As the hapticmakes direct contact with the lens capsule, the drug-containingmicrospheres are in the ideal location to prevent this new cell growth.Therefore any drug that prevents cell proliferation, inhibits cellmitosis or promotes cell apoptosis in the local environment will preventPCO and opacification of the optic. In the present invention an anti-PCOdrug has the above-mentioned properties. The intraocular lenses of thepresent invention thus have the advantage that no PCO occurs, no lasertreatment is required and thus will lead to higher patient comfort.

Also, laser treatment can be hardly performed on animals, such as catsor dogs, as the procedure is commonly done under local anesthesia withthe patient awake throughout the operation. However, animals, inparticular cats or dogs, tend to move, such that the success of a lasertreatment post-introduction of an intraocular lens is very low. Thus,the intraocular lenses of the present invention, in view of theirreduced risk of PCO, is beneficial for the treatment of animals, inparticular cats and dogs.

The intraocular lens according to the present invention may thuspreferably be used in the treatment of animals, in particular cats, dogsand horses.

The present invention also provides a method for manufacturing anintraocular lens, the method comprising the steps of:

i) providing drug-containing microspheres;ii) providing a precursor intraocular lens;iii) activating the microspheres and/or the precursor intraocular lens;andiv) attaching the microspheres to the precursor or activated intraocularlens. The microspheres may be attached to at least one or more hapticsof the precursor or activated intraocular lens.

Such a method for preparing the intraocular lens comprising microspheresattached thereto is schematically shown in FIG. 2. Therein, themicrospheres are formed (step S1) and surface activation is performedthereon (step S2). Separately, the precursor intraocular lens isactivated (step S3). The precursor intraocular lens denotes a regular orconventional intraocular lens, e.g. one that may be commerciallyavailable. The precursor intraocular lens denotes an intraocular lensnot having drug-containing microspheres attached thereto. Finally, boththe activated microspheres are attached to the activated intraocularlens (step S4).

The microspheres can be prepared by any known method including solventevaporation method, spray drying, dialysis and phase separation. In apreferred embodiment, the microspheres are formed by the solventevaporation method. The solvent evaporation method can be easilyoptimized, resulting in excellent control over the diameter and shape ofthe microspheres formed.

A method for preparing microspheres using a solvent evaporationtechnique and LLA, PLLA and PLGA is described in “Adv Drug Deliv Rev.1997 Oct. 13; 28(1):25-42. McGinity J W, O'Donnell PB.” The solventevaporation technique involves dissolving the polymers in a suitableimmiscible solvent, the solution is then agitated in an aqueous solutionresulting in emulsification. Microspheres are then formed from thehardening polymers as the solvent evaporates at the air/water interface.Difficulties with limited options for scale up, wide microspherediameter distribution, and harsh physical burdens can diminish theactivity of the drugs using these methods in comparison with the fairlymild solvent evaporation method.

In the solvent evaporation method, an emulsion is formed by dissolving apolymer into volatile organic solvent (also sometimes denoted as oillayer). This is then added to an aqueous layer with vigorous agitationto form an emulsion. As the volatile solvent evaporates, smallmicroparticles are prepared. A component (such as, drug, dye or protein)can be encapsulated by addition thereof into the polymer oil mixture(polymer solvent mixture). One or more different drugs may beencapsulated by this method into the same microcapsule. Otherwise,several microcapsules, each containing a different drug may be preparedby performing the method several times with different drugs. In order toimprove encapsulation, double emulsions can be prepared. Doubleemulsions are prepared by adding an initial emulsion into another phase.Most commonly to increase solubility of water soluble drugs,water/oil/water double emulsions are prepared. The first water in oilemulsion is prepared before being added into a larger water phasecreating a water/oil/water double emulsion.

For example, a first polymer such as poly(vinyl alcohol) is added todeionized water. Biodegradable polymers, such as a mixture of PLLA:PLGAis dissolved in a solvent such as dichloromethane (DCM). The desireddrug is then added into the biodegradable polymer in solvent solutionand emulsified. The emulsified solution is added to the rapidly stirringfirst polymer solution and the mixture stirred to allow solventevaporation. The solution is then transferred to a centrifuge tube andcentrifuged. The first polymer solution is then decanted off and themicrospheres washed in deionized water. The microspheres are isolated byfiltration and dried in a vacuum desiccator.

The type and amount of drug can be adjusted according to the requiredtreatment.

A typical setup for the preparation of microspheres by the solventevaporation technique is depicted in FIG. 3: 1) The polymer is dissolvedin an oil layer. 2) Agitation or mixing is required to split the oildroplets when in solution. 3) Water layer. 4) Oil/polymer droplets insolution. 5) Solvent evaporation occurs resulting in solid microspheresremaining.

Scanning electron micrographs are shown in FIG. 4, of 50:50 PLLA:PLGAmicrospheres prepared using the solvent evaporation technique (A)Original magnification×600; (B) Original magnification×2700.

In a preferred embodiment, the method thus includes activating themicrospheres including applying one of sodium hydroxide and a diaminolinker to the microspheres.

In a further preferred embodiment, activating the microspheres includesapplying one of sodium hydroxide and a diamino linker to themicrospheres.

Once the drug has been encapsulated the surface of the microsphere canbe reacted to allow for reaction onto the lens, such as an acrylic lens,at a later stage. For the microsphere activation, any route known in theart for activation of polymeric materials can be used.

A first preferred route that can be used in the present invention is touse sodium hydroxide to break the polymer structure of the microspheresto form an acid group which can be reacted further (cf. Scheme 1. Aabove).

A second preferred route that can be used in the present invention is touse a diamino linker, which activates the surface to give a free aminewhich can be reacted further (cf. Scheme 1. B above). This free aminegroup on the microspheres can be used to react with the intraocularlens, in particular an acrylic intraocular lens. These lenses aresusceptible to hydrolysis due to the esters present. The intraocularlens can firstly be broken down using acidic conditions and then thefree acid chains on the acrylic can be coupled to the microspheres usingaddition of base.

Thus, the activation of the microspheres may be performed by usingsodium hydroxide or a diamino linker.

The activation of the intraocular lens and the attachment of themicrospheres to the intraocular lens can be performed as follows.

This free amine group on the microspheres can be used to react with theacrylic intra ocular lens (IOL). These lenses are susceptible tohydrolysis due to the esters present. The intraocular lens can firstlybe broken down using acidic conditions and then the free acid chains onthe (acrylic) intraocular lens can be coupled to the microspheres.Alternatively additional base could be added directly to the lens, whichwould ensure that the primary amine on the microsphere remains basic andcould be reacted directly with the acrylic.

In a preferred embodiment, the microspheres are thus attached byreacting at least an acid group or an amine group on the microsphereswith reactive groups on the intraocular lens (such as ester or acidgroups, which may have been used to cap the polymer chains of anacrylic).

In a preferred embodiment of the method, the microspheres are attachedonly to the haptics of the intraocular lens. In order to attach themicrospheres only to the haptics, only the reactive groups in the hapticwill be reacted with either the acid or base conditions to react withthe reactive group on the microspheres. This may be done by e.g.physically keeping the optic outside the reaction conditions, i.e. notin the solvent with the drug-containing microspheres.

In a preferred embodiment, attaching the microspheres includes reactingone of an acid group and an amine group on the microspheres with one ormore reactive groups on the precursor intraocular lens.

The intraocular lenses as described in this invention can be used forthe treatment of diseases. The intraocular lenses with controlledrelease according to the present invention may in particular be used forthe treatment of cataract.

The present invention also provides a method for cataract treatment orglaucoma, comprising: providing an intraocular lens including aplurality of drug-containing microspheres attached to the intraocularlens (e.g. one or more haptics of the intraocular lens); inserting theintraocular lens into a capsular bag of an eye to be treated; andcausing one or more drugs contained in the microspheres to be releasedinto the eye.

In the above description, it has been shown how intraocular lenses (IOB)can be prepared that can release a drug in a defined manner. Theintraocular lenses may thus have controlled release or drug elutingproperties.

The invention provides a drug-containing microsphere which is attachedto the intraocular lens, allowing controlled release of antibiotic,anti-inflammatory and anti-proliferative drugs within an animal eye overa prolonged period of time.

By attaching microspheres to the haptics of the intraocular lens, drugscontained in the microspheres can be controllably released to the sitein the eye where they are required over a prolonged period of time.

In case the drug-containing microspheres are only attached to the one ormore haptics of the intraocular lens, this assures that no cloudy visionor visual impairment is caused. As compared to eye drops, which areadministered to the eye on a frequent basis and of which theadministration can be hardly controlled, the device of the presentinvention allows providing a drug in a defined manner to only the regionof the eye where it is required, without any drawbacks on the vision.Also, with eye drops, it is hard to control the concentration of drugadministered. Similarly, injection of a drug is unpleasant for thepatient and control of the concentration is hardly achieved.

This effect may in particular be preferable for the use after cataractsurgery. The controlled drug release occurs through degradation of themicrospheres that is tailored to the treatment course of each individualdrug.

The intraocular lens according to the present invention reduces the riskof inflammation, infection and PCO. By improving patient outcomes,obviating the need for eye drops after surgery, and avoiding a secondsurgical procedure.

The intraocular lens according to the present invention also preventspost capsular opacification (PCO) and removes the need for eye dropsfollowing cataract surgery.

The intraocular lens having the controlled drug release confer animprovement, such as at least an 10-30% improvement in patient outcomesover standard care, therefore making it an attractive device forhealthcare providers and results in tangible improvements for thepatient.

The attachment of the microspheres to intraocular lenses thereforereduces the need for recurrent surgery, follow-up treatment orpostoperative eye-drops.

This intraocular lens according to the present invention prevents newcell growth over the lens capsule and reduces the need for furthertreatment, benefiting patients and healthcare providers. The intraocularlens also incorporates antibiotic and anti-inflammatories (usuallyadministered as eye drops post-surgery) to reduce problems associatedwith patient non-compliance.

The intraocular lens has the advantage that no treatment includingtopically administered eye drops is required, as the drug required postcataract surgery is included in the intraocular lens and administeredover time.

The microspheres can be designed to encapsulate different drugs to treatdifferent conditions and the drug release timings can be modified tosuit need. The technique to prepare the microspheres may be the same foreach drug. However, by altering the size, PLGA/PLLA ratio, the averagemolecular weight of the PLGA/PLLA in the microspheres, etc. the releasemay be tuned individually for each type of drug. In a preferredembodiment, only one drug may be encapsulated in the microspheres and acombination of different drug-containing microspheres may be attached tothe at least one haptics.

Experimental Results Microsphere Preparation

The microspheres have been prepared using the conditions below:

Poly(vinyl alcohol) (0.05 g, RMM 31,000-50,000, Sigma-Aldrich) was addedto deionized water (50 mL) and the mixture was rapidly stirred (2500rpm). w:w ratios of PLLA (Resomer L 205, i.v. 0.8-1.2 dL g-1, 0.1% inchloroform, 25° C., RMM˜100,000 obtained from Boehringer Ingelheim) andPLGA (Resomer RG 755 S, i.v. 0.5-0.7 dL g-1, 0.1% in chloroform, 25° C.,RMM˜20,000-80,000 obtained from Boehringer Ingelheim) having a totalmass of 0.1 g were dissolved in dichloromethane (DCM) (4 mL). The drug(e.g. 1.25 μg, 0.05 mL) was then added in to the PLLA:PLGA in DCMsolution and emulsified for 1 minute to 10 minutes. The PLLA:PLGA DCMsolution was then added to the rapidly stirring PVA solution and themixture was left to stir for 20 min to allow solvent evaporation. Thesolution was then transferred to a centrifuge tube and centrifuged for 4min at 4000 rpm. The PVA solution was then decanted off and themicrospheres were washed 3 times in deionized water. The microsphereswere then isolated by filtration and dried in a vacuum desiccator.

Activation of Microspheres

Microspheres (0.15 g) were added to a premade solution (26 mL) of1,3-diaminopropane (268 μL) in IPA (32 mL). The solution was heated at40° C. in a sand bath for 15 min before being washed with water (6×40mL) and dried under vacuum.

Microsphere Attachment

The Haptic of the intraocular lens was added to a weak HCl solution for15 min before being washed with water. The activated microspheres wereadded in various ratios to the activated acrylic with 1 drop oftriethylamine and reacted. These were then washed with DI water.

Test of Biodegradability of the Microspheres

The biodegradability was analyzed by SEM and indirectly by release ofthe drug. Once all the drug was released this was taken as indicationthat the microspheres had fully degraded.

Test of Release Rate of Microspheres Attached to an Intraocular Lens

Encapsulated microspheres attached to the intraocular lens were addedinto centrifuge tubes (Fisher Scientific) with phosphate buffered saline(PBS 0.01 M, 1 mL, pH 7.4, Sigma-Aldrich). The sealed tubes were kept at37° C. and at set intervals the microspheres were centrifuged and thesupernatant was collected for sampling after filtration through a 0.45μm syringe filter (Fisher Scientific). The concentration of the drug wasthen determined measuring absorbance on a UV spectrometer against acalibration curve. Fresh PBS (1 mL) was added to the centrifuge tubesand placed back at 37° C.

1-15. (canceled)
 16. A composition comprising: a first material that isselected from an acrylate, a fluorinated polymer, a polyimide, acollamer, a silicone, or a polyolefin; and a second material that is abiodegradable polymer selected from the group consisting ofpoly(L-lactic acid) (PLLA), poly(lactic-co-glycolic acid) (PLGA) andcombinations thereof, and comprises at least one encapsulated compound;wherein the first material is attached covalently via an acid or anamine group to the second material, and wherein the encapsulatedcompound is a drug and is controllably released over a period of time.17. The composition of claim 16, wherein the biodegradable polymercomprises a mixture of PLLA and PLGA.
 18. The composition of claim 16,wherein the first material further comprises an acrylate selected fromthe group consisting of a polymethylmethacrylate (PMMA), a hydrophobicacrylate and a hydrophilic acrylate.
 19. The composition of claim 16,wherein the covalent attachment is via a peptide bond.
 20. Thecomposition of claim 16, wherein the second material is surfaceactivated by treatment with sodium hydroxide prior to covalentattachment.
 21. The composition of claim 16, wherein the second materialis reacted with a diamino compound so as to provide a free amine groupprior to covalent attachment.
 22. The composition of claim 16, whereinthe first material is surface activated via treatment under acidicconditions prior to covalent attachment.
 23. The composition of claim16, wherein the covalent attachment comprises a linker.
 24. Thecomposition of claim 23, wherein the linker comprises an acid or anamino group.
 25. The composition of claim 23, wherein the linkercomprises an alkyl chain.
 26. The composition of claim 16, wherein thefirst material is comprised within an intraocular lens.
 27. Anintraocular implant comprising: a first material that is selected froman acrylate, a fluorinated polymer, a polyimide, a collamer, a silicone,or a polyolefin; and a second material that is a biodegradable polymerselected from the group consisting of poly(L-lactic acid) (PLLA),poly(lactic-co-glycolic acid) (PLGA) and combinations thereof, andcomprises at least one encapsulated drug compound; wherein the firstmaterial is attached covalently via an acid or an amine group to thesecond material, and wherein the encapsulated drug compound iscontrollably released from the implant over a period of time after asurgical implantation.
 28. The intraocular implant of claim 27, whereinthe biodegradable polymer comprises a mixture of PLLA and PLGA.
 29. Theintraocular implant of claim 27, wherein the first material comprises anacrylate selected from the group consisting of a polymethylmethacrylate(PMMA), a hydrophobic acrylate and a hydrophilic acrylate.
 30. Theintraocular implant of claim 27, wherein the covalent attachment is viaa peptide bond.
 31. The intraocular implant of claim 27, wherein theimplant is an intraocular lens.
 32. The intraocular implant of claim 31,wherein the intraocular lens comprises one or more haptics.
 33. Theintraocular implant of claim 27, wherein the encapsulated drug compoundis selected from an antibiotic, an anti-inflammatory, ananti-hypertensive, an anti-glaucoma, or an anti-proliferative agent. 34.The intraocular implant of claim 27, wherein the encapsulated drugcompound is controllably released for at least one day after a surgicalimplantation.
 35. The intraocular implant of claim 27, wherein theencapsulated drug compound is controllably released for at least oneweek after a surgical implantation.